|Número de publicación||US7507211 B2|
|Tipo de publicación||Concesión|
|Número de solicitud||US 10/990,654|
|Fecha de publicación||24 Mar 2009|
|Fecha de presentación||17 Nov 2004|
|Fecha de prioridad||26 Dic 2001|
|También publicado como||US6799067, US6845259, US20030120148, US20030135114, US20050070793, WO2003057302A1|
|Número de publicación||10990654, 990654, US 7507211 B2, US 7507211B2, US-B2-7507211, US7507211 B2, US7507211B2|
|Inventores||Stephen D. Pacetti, Douglas H. Gesswein, Emmanuel C. Biagtan|
|Cesionario original||Advanced Cardiovascular Systems, Inc.|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (54), Otras citas (9), Citada por (4), Clasificaciones (13), Eventos legales (4)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
This is a continuation of application Ser. No. 10/335,783, filed Jan. 2, 2003, now U.S. Pat. No. 6,845,259,which is a continuation of application Ser. No. 10/034,715, filed Dec. 26, 2001, now U.S. Pat. No. 6,799,067, all of whose contents are hereby incorporated by reference.
This invention relates generally to the field of medical devices, and more particularly to a guide wire for advancing a catheter or other intraluminal device within a body lumen in a procedure such as percutaneous transluminal coronary angioplasty (PTCA) or stent delivery which is observed by Magnetic Resonance Imaging (MRI).
Conventional guide wires for angioplasty and other vascular procedures usually comprise an elongated core member with one or more tapered sections near the distal end thereof and a flexible body such as a helical coil disposed about the distal portion of the core member. A shapeable member, which may be the distal extremity of the core member or a separate shaping ribbon which is secured to the distal extremity of the core member, extends through the flexible body and is secured to a rounded plug at the distal end of the flexible body. Torquing means are provided on the proximal end of the core member to rotate, and thereby steer, the guide wire while it is being advanced through a patient's vascular system.
In a typical PTCA procedure, a guiding catheter having a preformed distal tip is percutaneously introduced into the cardiovascular system of a patient in a conventional Seldinger technique and advanced therein until the distal tip of the guiding catheter is seated in the ostium of a desired coronary artery. A guide wire is positioned within an inner lumen of a dilatation catheter and then both are advanced through the guiding catheter to the distal end thereof. The guide wire is first advanced out of the distal end of the guiding catheter into the patient's coronary vasculature until the distal end of the guide wire crosses a lesion to be dilated, then the dilatation catheter having an inflatable balloon on the distal portion thereof is advanced into the patient's coronary anatomy over the previously introduced guide wire until the balloon of the dilatation catheter is properly positioned across the lesion. Once in position across the lesion, the balloon is inflated to a predetermined size with radiopaque liquid at relatively high pressures (e.g., greater than 4 atmospheres) to press the arteriosclerotic plaque of the lesion against the inside of the artery wall and to otherwise expand the inner lumen of the artery. The balloon is then deflated so that blood flow is resumed through the dilated artery and the dilatation catheter can be removed therefrom.
A major requirement for guide wires is that they have sufficient column strength to be pushed through a patient's vascular system or other body lumen without kinking. However, they must also be flexible enough to avoid damaging the blood vessel or other body lumen through which they are advanced. Efforts have been made to improve both the strength and flexibility of guide wires to make them more suitable for their intended uses, but these two properties are for the most part diametrically opposed to one another in that an increase in one usually involves a decrease in the other.
Currently, x-ray fluoroscopy is the preferred imaging modality for cardiovascular interventional procedures because no other imaging method has the temporal or spatial resolution provided by fluoroscopy. However, x-ray imaging has many drawbacks for both the patient and the clinician. The iodinated contrast agents employed in x-ray fluoroscopy are nephrotoxic with a low but measurable incidence of short-term renal failure and allergic reactivity. The ionizing radiation from the x-ray fluoroscopy can be an issue for the patient during protracted or repeated interventions and is a daily issue for the interventionalist and staff who must cope with the burden of personal dose monitoring and wearing lead shielding.
The use of MRI for observing interventional procedures has been performed for balloon angioplasty and stent placement. The use of this imaging modality is quite attractive because it eliminates some of the problems inherent with x-ray imaging. On the other hand, conventional guide wires which are suitable for x-ray fluoroscopy are not suitable for use in MRI observed interventional procedures due to their magnetic attraction, large magnetic susceptibility artifact, and potential heating when exposed to RF energy.
What has been needed and heretofore unavailable is a guide wire which is safe and compatible for use in conjunction with MRI. The present invention satisfies these and other needs.
The present invention is directed to an intracorporeal device such as a guide wire which is safe, compatible and readily visible with MRI. An intracorporeal device embodying features of the invention preferably has an elongated member with an electrically non-conductive proximal section, an essentially non-magnetic distal core section, and a metallic coil disposed about and secured to the distal core section with a small magnetic susceptibility to act as an MRI visible marker. That is, the coil or a marker thereon has a magnetic susceptibility that facilitates the observation thereof within the patient under MRI.
The distal end of the proximal non-conductive core section and the proximal end of the non-magnetic but conductive distal core section can be secured together by any non-conductive means including polymeric or metallic sleeves so long as the joint between these members results in a torque transmitting relationship therebetween.
The selection of materials for component parts of the intracorporeal device, such as a guide wire, including the proximal section, the distal section and the MRI visible member secured to the distal section are based upon the mechanical and physical properties needed for the intended use. The materials from which the MRI compatible device is made need to overcome three basic factors: magnetic attraction of magnetic members, RF heating effects of conductive members, and visualization under MRI.
Forming the proximal section from non-conductive, non-metallic material and the distal section and MRI visible member from non-magnetic materials resolves the magnetic attraction of these members during MRI. The non-conductive, non-metallic nature of the proximal core section and the length of the distal core section alone or in conjunction with the MRI visible member resolve the RF heating of these members. Controlling the level of magnetic susceptibility of the material from which the MRI visible member is formed resolves the visualization issue.
Suitable materials for the non-conductive proximal section of the intracorporeal device include optical fibers (single or a bundle of fibers), fiberglass, carbon fiber-epoxy composites, composites of oriented polyethylene fiber (e.g., Spectra®), composites of polyaramide fiber (e.g., Kelvar®) and composites of these materials with engineering resins such as polysulfone, polyethersulfone, polyetherimide, vinylester, cyanate ester, phenolic, polyurethane, polyimide and polyetheretherketone. The MRI visible member or marker and preferably also the distal section are formed of suitable non-magnetic materials that may be electrically conductive. Suitable materials include one or more metallic materials selected from the group consisting of platinum, nitinol, niobium, titanium, tantalum, zirconium, iridium, aluminum, silver, gold, indium, and alloys thereof.
The distal core section and the tip coil are formed of suitable non-magnetic conductive materials having the correct amount of magnetic susceptibility artifact for accurate imaging. The volumetric magnetic susceptibility suitable for visualization under MRI for these structures is less than or equal to about 280×10−6 (SI), and preferably less than about 245×10−6 (SI).
The intracorporeal devices embodying features of the present invention are in part readily visible under MRI and they have desirable characteristics for performing intracorporeal procedures. These and other advantages of the invention will become more apparent from the following detailed description thereof when taken in conjunction with the following exemplary drawings.
The guide wire 10 shown in
The polymeric connecting element 13, which is shown in detail in
The connection between the ends 20 and 21 of the proximal and distal core sections 11 and 12, respectively, may be made by positioning the distal end 20 of the proximal core section 11 and the proximal end 21 of the distal core section 12 in close proximity to each other within the interior of a mold which preferably has a cylindrical interior molding surface of the desired dimensions of the exterior surface 22 of the connecting member 13. Polymerizable or otherwise hardenable non-conductive material is introduced into the interior of the mold and polymerized or otherwise hardened into a polymeric or other non-metallic mass about the ends 20 and 21 so as to fix the ends within the connecting element 13. The hardenable non-conductive material forming the connection between the proximal and distal core sections 11 and 12 is sufficiently strong to facilitate torque transmission between these core sections.
Suitable non-magnetic, and preferably polymeric materials for the connecting element 13 include one or more thermoplastic polymeric materials such as a polyester, polyetheretherketone, ABS, and epoxy materials or co-polymers or blends thereof. The polymeric materials may be blends of a variety of polymeric materials. The polymeric material is preferably selected so that the connecting element 13 holds the two core sections together to effect torque transmission and to provide a smooth transition between the proximal and distal core sections 11 and 12, respectively. It will be appreciated that, in light of the foregoing, and of the fact that the connector element 13 of this embodiment has a cylindrical exterior 22 that has an outer diameter about the same as the outer diameter of the proximal core section 11, and further as exemplified in
The proximal section 11 of one embodiment of the guide wire 10 is fabricated from metals such as work hardened 304V stainless steel. In order to have similar tracking, torque, and push properties, proximal sections of polymeric and composite materials would ideally have similar properties. One important property to match is stiffness both laterally and axially while hardness is of lesser importance. To achieve the preferred properties of a guide wire, any proximal shaft of a polymeric material would be a composite. Further, the polymer component may be a thermoset or a thermoplastic. Exemplary of common thermosets include epoxy, polyester, vinylester, cyanate ester, phenolic, polyurethane, and polyimide. Suitable fiber reinforcement materials include fiberglass, s-glass, e-glass, graphite, Kevlar®, Twaron®, Nomex®, Spectra®, polyaramid, carbon, boron, and boron nitride.
Fiberglass components may also be used in fabricating the guide wire, recognizing that fiberglass is typically a composite of a polyester resin with a glass fiber reinforcement. Guide wires fabricated entirely from fiberglass, however, do not have the functional advantages of a distal metallic section 12 and metallic tip coil 17.
Composite guide wire structures of fiber reinforced polymeric materials may be made by methods of extrusion, pultrusion, injection molding, transfer molding, flow encapsulation, fiber winding on a mandrel, or lay up with vacuum bagging. Epoxy resins are available from a variety of manufacturers including Ciba Specialty Chemicals, Shell Chemical, Dow Chemical, and Gougeon Brothers, Inc. Sources of carbon fiber include Hexcel Corp., Amoco, Toho, Rayon, and Toray. Exemplary of non-composite materials for the non-conductive proximal section 11 include glass fiber optics (available from Corning Glass and Seiko Instruments, Inc.) and ceramics.
The examples set forth in detail below illustrate the fabrication of a composite proximal shaft of a guide wire in accordance with the present invention. In the first exemplary embodiment, a composite proximal shaft is fabricated with IM7 carbon fibers (available from Hexcel Corp.) and an Epon epoxy resin system (available from Shell Corp.). Using pultrusion, a shaft of 67 volume percent carbon fiber is fabricated. A 20 cm distal section of nitinol is affixed to the shaft using a sleeve joint. A tip coil of 90/10 tantalum/tungsten alloy is attached by soldering to the distal end of the nitinol section.
In the second exemplary embodiment, a composite proximal shaft is fabricated of Victrex™ PEEK 450CA30 (30% carbon reinforced) by extrusion. Optional bands of palladium are attached to the shaft at 10 cm intervals to function as passive paramagnetic susceptibility markers. The 20 cm distal metallic shaft is fabricated of CP (commercially pure) titanium (Wah Chang). A 90/10 platinum/iridium tip coil is attached via soldering to the titanium section.
As seen in
The non-electrically conductive proximal core section 11 is MRI safe with regard to both attractive forces and RF heating effects. This distal core section 12 between the non-conductive proximal core section 11 and the tip coil 27 is analogous to the distal nitinol section of a conventional guide wire. Its maximum safe length can be estimated from the magnetic field strength of the MRI scanner. At 1.5 T, antenna theory predicts that a guide wire can behave as a dipole antenna beginning at a length of 23 inches (about 58 cm).
Preferably, the metallic tip coil 27 and the distal core section 12 (the conductive members) are connected with a non-conductive insulator so that they do not act in concert as a single dipole antenna. If the metallic tip coil 27 and the distal core section 12 are separated by a non-conductive material 13, then the length of the distal core section 12 can be up to 23 cm in a magnetic field of 1.5 T. Without the insulator, the 23 cm length applies to the total length of the tip coil 27 and the distal core section 12.
As the RF frequency utilized is linearly proportional to the MRI scanner field strength, lower field strengths of 1.0 T and 0.5 T couple at conductor member lengths of 35 cm and 69 cm, respectively. So at a lower magnetic field strength of 1.5 T, a preferred range for the length of the conductive member is less than 29 cm. A more preferred range of the length of the conductive member is less than 23 cm. The minimum practical length of the conductive section is determined by the length of a functional guide wire tip coil which is approximately 3 cm. These maximum safe lengths are inversely proportional to the magnetic field strength.
The highest field strength MRI scanners in routine clinical use at the present time operate at 3 T. At this strength, a preferred conductor length is less than approximately 14.4 cm, and a more preferred conductor length is less than approximately 11.5 cm. Thus, as the MRI scanner field strength increases, the safe length of the conductive members decreases.
Accordingly, the conductive member in one embodiment has a length of about L<43.5/B0, where “L” represents the electrically conductive length in centimeters, and “B0” represents the scanner magnetic field in Tesla. In a more preferred embodiment, the conductive member has a length of about L<34.5/B0. The experimental and theoretical foundation for these values may be found in the work of Liu et al., Journal of Magnetic Resonance Imaging, Vol. 12, pp. 75-78 (2000), and Nitz et al., Journal of Magnetic Resonance Imaging, Vol. 13, pp. 105-114 (2001), the contents of which are incorporated herein by reference.
The electrical conductivity of the non-conductive proximal core section 11 is electrical resistivity expressed in micro-ohm-cm. The higher the value for electrical resistivity, the more resistance for the material of the proximal core section. Based on research using nitinol guide wires, for example, it has been found that at about 100 micro-ohm-cm, a nitinol guide wire is conductive enough to heat in an MRI scanner. However, little research has been done examining how conductive a long wire can be in an MRI and still avoid heating. Models of this effect have considered resistance of the wire to be negligible. The minimum resistivity for the non-conductive proximal core section is estimated to be approximately 0.01 ohm-cm.
The coil 16 may also be formed by two separate coil segments: a distal coil segment 27 which is formed of a non-magnetic material having the requisite magnetic susceptibility to provide MRI visibility, and a proximal coil segment 28 which may be made of another material having other desirable properties such as radiopacity. Additionally, the distal coil segment 27 of the coil 16 may be stretched about 10 to about 30% in length as shown in
The elongated proximal core section 11 may be an optical fiber which should be provided with a coating 30 of lubricous material such as a fluoropolymer, polytetrafluoroethylene sold under the trademark Teflon® by Du Pont de Nemours & Co. Other suitable lubricous coatings include fluoropolymers, hydrophilic coatings and polysiloxane coatings.
The overall length of the guide wire 10 will vary depending upon the procedure and the MRI compatibility parameters mentioned above, but for percutaneous intravascular procedures the guide wire is generally about 100 to about 200 cm in length. Most commercially available guide wires for adult coronary use come in lengths of 175 cm and 195 cm. The outer diameter of the guide wire ranges from about 0.006 to 0.018 inch (0.15-0.45 mm) for coronary use. Larger diameter guide wires, e.g. up to 0.035 inch (0.89 mm) or more may be employed in peripheral arteries and other body lumens. The length of the distal core section can range from about 1 to about 30 cm, depending upon the flexibility and other properties including MRI imaging characteristics desired in the final product. The helical coil 16 may be about 3 to about 45 cm in length, preferably about 5 to about 30 cm and may have an outer diameter about the same size as the outer diameter of the elongated proximal core section 11. The helical coil 16 is preferably made from wire about 0.001 to about 0.003 inch (0.025-0.08 mm) in diameter, typically about 0.002 inch (0.05 mm). The shaping ribbon 21 and the flattened distal section 29 of distal core section 12 can have generally rectangular shaped transverse cross-sections which usually have dimensions of about 0.0005 to about 0.006 inch (0.013-0.152 mm), and preferably about 0.001 by 0.003 inch (0.025-0.076 mm).
In an embodiment of the present invention, the distal core section 12 is made of a metal or alloy material which has a volumetric magnetic susceptibility of less than about 280×10−6 (SI), and preferably less than about 245×10−6 (SI). Metals that meet this criteria and their respective volumetric magnetic susceptibility are set forth in the following table. While the distal core section 12 needs to be essentially non-magnetic, it does not necessarily require the volumetric magnetic susceptibility set forth above which provides visibility under MRI.
SUSCEPTIBILITY (× 10−6 (SI))
Various polymeric connecting elements 13 embodying features of the invention generally have outer diameters from about 0.006 inch to about 0.02 inch (0.15-0.51 mm), and preferably about 0.10 to about 0.014 inch (2.5-0.356 mm) for coronary guide wires. The overall length of the connecting element 13 may range from about 0.25 to about 3 cm, and typically ranges about 0.75 to about 1.5 cm. Naturally, the connecting elements for guide wires for other medical applications and treatment sites may have dimensions different than that described above.
The proximal core section 11 is formed of a non-conductive material such as an optical fiber (e.g., a single fiber or a bundle of fibers), carbon fiber epoxy composites, composites of oriented polyethylene fiber (e.g., Spectra®), composites of polyaramide fiber (e.g., Kelvar®), and composites of these materials with engineering resins such as polyaryetherketone, polyphenylenesulfide, polyimide and polyetheretherketone. Other suitable non-conductive materials may be used for the proximal core section.
The guide wire embodying features of the invention may be percutaneously introduced into a patient's blood vessel, such as the femoral artery, and advanced within the patient's vasculature under MRI so as to be able to observe the coil at the guide wire distal core section which acts as an MRI visible marker member to ensure that the guide wire or other intracorporeal device is disposed at a desired location within the patient's vasculature. Once the distal portion of the guide wire is in place at the desired location, a therapeutic or diagnostic device may be advanced over the in place guide wire until the operative portion of the intracorporeal device is positioned to perform a therapeutic or diagnostic procedure in a conventional fashion.
While the description of embodiments having features of the invention has been directed primarily herein to guide wires suitable for guiding other devices within a patient's body, those skilled in the art will recognize that these features may also be utilized in other intracorporeal devices such as electrophysiology catheters, pacing leads and the like. References to other modifications and improvements can be made to the invention without departing from the scope of the appended claims.
To the extent not otherwise described herein, the materials and methods of construction and the dimensions of conventional intracorporeal devices such as intravascular guide wires may be employed with a device embodying features of the present invention. Moreover, features disclosed with one embodiment may be employed with other described embodiments. Additionally, reference to the terms “members,” “elements,” “sections” and terms of similar import in the claims which follow shall not be interpreted to invoke the provisions of 35 U.S.C. § 112 (paragraph 6) unless reference is expressly made to the term “means” followed by an intended function.
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US2857915||2 Abr 1956||28 Oct 1958||Sheridan David S||X-ray catheter|
|US3485234||13 Abr 1966||23 Dic 1969||Cordis Corp||Tubular products and method of making same|
|US3529633||23 Oct 1967||22 Sep 1970||Bard Inc C R||X-ray opaque tubing having a transparent stripe|
|US3585707||1 Abr 1969||22 Jun 1971||Cordis Corp||Method of making tubular products|
|US3608555||31 Dic 1968||28 Sep 1971||Chemplast Inc||Radio opaque and optically transparent tubing|
|US3994607 *||11 Sep 1974||30 Nov 1976||The Furukawa Electric Co., Ltd.||Connector for fiber reinforced plastic wire|
|US4966163 *||14 Feb 1989||30 Oct 1990||Advanced Cardiovascular Systems, Inc.||Extendable guidewire for vascular procedures|
|US4989608||28 Abr 1989||5 Feb 1991||Ratner Adam V||Device construction and method facilitating magnetic resonance imaging of foreign objects in a body|
|US5061395||4 Ene 1990||29 Oct 1991||Ques Industries, Inc.||Hard surface cleaning composition|
|US5154179||22 Ene 1991||13 Oct 1992||Medical Magnetics, Inc.||Device construction and method facilitating magnetic resonance imaging of foreign objects in a body|
|US5409015||11 May 1993||25 Abr 1995||Target Therapeutics, Inc.||Deformable tip super elastic guidewire|
|US5439000||18 Nov 1993||8 Ago 1995||Spectrascience, Inc.||Method of diagnosing tissue with guidewire|
|US5479938||7 Feb 1994||2 Ene 1996||Cordis Corporation||Lumen diameter reference guidewire|
|US5487739||2 Jun 1995||30 Ene 1996||Brown University Research Foundation||Implantable therapy systems and methods|
|US5516336||18 Ene 1994||14 May 1996||Advanced Cardiovascular Systems, Inc.||Readily exchangeable perfusion dilatation catheter|
|US5573508 *||22 Nov 1994||12 Nov 1996||Advanced Cardiovascular Systems, Inc.||Catheter with an expandable perfusion lumen|
|US5601087||7 Jun 1995||11 Feb 1997||Spectrascience, Inc.||System for diagnosing tissue with guidewire|
|US5637089||12 Feb 1996||10 Jun 1997||Advanced Cardiovascular Systems, Inc.||Superelastic guiding member|
|US5769796||22 Ene 1997||23 Jun 1998||Target Therapeutics, Inc.||Super-elastic composite guidewire|
|US5792055||19 Nov 1996||11 Ago 1998||Schneider (Usa) Inc.||Guidewire antenna|
|US5824055||25 Mar 1997||20 Oct 1998||Endotex Interventional Systems, Inc.||Stent graft delivery system and methods of use|
|US5848964||6 Jun 1997||15 Dic 1998||Samuels; Shaun Lawrence Wilkie||Temporary inflatable filter device and method of use|
|US5897536||23 Sep 1997||27 Abr 1999||Cordis Europa, N.V.||Catheter having a controllable stiffness and adapted for use with various contrast media|
|US5947995||6 Ago 1998||7 Sep 1999||Samuels; Shaun Lawrence Wilkie||Method and apparatus for removing blood clots and other objects|
|US5951480||29 Sep 1997||14 Sep 1999||Boston Scientific Corporation||Ultrasound imaging guidewire with static central core and tip|
|US5951494||16 Ene 1997||14 Sep 1999||Boston Scientific Corporation||Polymeric implements for torque transmission|
|US5961511 *||28 Oct 1998||5 Oct 1999||Scimed Life Systems, Inc.||Catheter having LCP reinforced distal portion|
|US6001068 *||21 Oct 1997||14 Dic 1999||Terumo Kabushiki Kaisha||Guide wire having tubular connector with helical slits|
|US6014580||9 Feb 1998||11 Ene 2000||Stereotaxis, Inc.||Device and method for specifying magnetic field for surgical applications|
|US6019737||31 Mar 1998||1 Feb 2000||Terumo Kabushiki Kaisha||Guide wire|
|US6026316||15 May 1997||15 Feb 2000||Regents Of The University Of Minnesota||Method and apparatus for use with MR imaging|
|US6061587||15 May 1997||9 May 2000||Regents Of The University Of Minnesota||Method and apparatus for use with MR imaging|
|US6095990||31 Ago 1998||1 Ago 2000||Parodi; Juan Carlos||Guiding device and method for inserting and advancing catheters and guidewires into a vessel of a patient in endovascular treatments|
|US6106473||6 Nov 1997||22 Ago 2000||Sts Biopolymers, Inc.||Echogenic coatings|
|US6165139||1 Jun 1995||26 Dic 2000||Fonar Corporation||Remotely steerable guide wire with external control wires|
|US6165292||7 Jun 1995||26 Dic 2000||Advanced Cardiovascular Systems, Inc.||Superelastic guiding member|
|US6171240||5 Dic 1997||9 Ene 2001||Picker International, Inc.||MRI RF catheter coil|
|US6171250||10 Sep 1999||9 Ene 2001||Boston Scientific Corporation||Ultrasound imaging guidewire with static central core and tip|
|US6190353||11 Oct 1996||20 Feb 2001||Transvascular, Inc.||Methods and apparatus for bypassing arterial obstructions and/or performing other transvascular procedures|
|US6203568||24 Jul 1998||20 Mar 2001||Medtronic, Inc.||Endoluminal prostheses having position indicating markers|
|US6241703 *||27 May 1999||5 Jun 2001||Angiosonics Inc.||Ultrasound transmission apparatus having a tip|
|US6241744||16 Dic 1998||5 Jun 2001||Fox Hollow Technologies, Inc.||Apparatus for deploying a guidewire across a complex lesion|
|US6248076||25 Jul 2000||19 Jun 2001||Boston Scientific Corporation||Ultrasound imaging guidewire with static central core and tip|
|US6261246||28 Sep 1998||17 Jul 2001||Scimed Life Systems, Inc.||Intravascular imaging guidewire|
|US6261247||30 Dic 1999||17 Jul 2001||Ball Semiconductor, Inc.||Position sensing system|
|US6272370||7 Ago 1998||7 Ago 2001||The Regents Of University Of Minnesota||MR-visible medical device for neurological interventions using nonlinear magnetic stereotaxis and a method imaging|
|US6280539||7 Feb 2000||28 Ago 2001||Advance Cardiovascular Systems, Inc.||Superelastic guiding member|
|US6402706 *||30 Dic 1998||11 Jun 2002||Advanced Cardiovascular Systems, Inc.||Guide wire with multiple polymer jackets over distal and intermediate core sections|
|US6702762||27 Dic 2001||9 Mar 2004||Advanced Cardiovascular Systems, Inc.||Apparatus and method for joining two guide wire core materials without a hypotube|
|US6799067 *||26 Dic 2001||28 Sep 2004||Advanced Cardiovascular Systems, Inc.||MRI compatible guide wire|
|US6845259 *||2 Ene 2003||18 Ene 2005||Advanced Cardiovascular Systems, Inc.||MRI compatible guide wire|
|US6893456 *||22 Dic 2000||17 May 2005||Advanced Cardiovascular Systems, Inc.||Catheter and method for making the same|
|US6918882 *||5 Oct 2001||19 Jul 2005||Scimed Life Systems, Inc.||Guidewire with stiffness blending connection|
|US20040102720||25 Nov 2002||27 May 2004||Brad Kellerman||Enhanced method for joining two core wires|
|1||C. Manke et al., Stent Angioplasy of Iliac Artery Stenoses under MR-control: Initial Clinical Results, Fortschr Rontgenstr; 172: 92-97 (2000).|
|2||Chia-Ying Liu et al., Safety of MRI-Guided Endovascular Guidewire applications, JMRI 12:75-78 (2000).|
|3||Chris J. Bakker et al., MR-Guided Balloon Angioplasty: In Vitro Demonstration of the Potential of MRI for Guiding, Monitoring, and Evaluating Endovascular Interventions, JMRI, vol. 8, No. 1, 245-250 (1998).|
|4||John F. Schenck, The role of magnetic susceptibility in magnetic resonance imaging: MRI magnetic compatability of the first and second kinds, Med Phys. 23 (6), 816 850 (1996).|
|5||L.W. Bartels et al., MR-guided Balloon Angioplasty of Stenosed Hemodialysis Access Grafts, Proc. Intl. Soc. Mag. Reson. Med. 8, 409 (2000).|
|6||Lee P. Bendel et al., The Effect of Mechanical Deformation on Magnetic Properties and MRI Artifacts of Type 304 and Tupe 316L Stainless Steel, JMRI, vol. 7, No. 6 1170 1173 (1997).|
|7||Maurits K. Kongings et al., Heating Around Intravascular Guidewires by Resonating RF Waves, JMRI, vol. 12, No. 1, 79-85 (2000).|
|8||Paul R. Hilfiker et al., Plain and Covered Stent-Grafts: In Vitro Evaluation of Characteristics at Three-dimensional MR Angiography, Radiology, vol. 211, No. 3 693-697 (1999).|
|9||Wolfgang R. Nitz et al., On the Heating of Linear Conductive Structures as Guide Wires and Catheters in Intervnentional MRI, JMRI 13:105-114 (2001).|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US20080058789 *||5 Sep 2007||6 Mar 2008||Cardiofirst||Guidance system used in treating chronic occlusion|
|US20100207291 *||13 Feb 2009||19 Ago 2010||Boston Scientific Scimed, Inc.||Method of Making a Tubular Member|
|US20120245488 *||8 Feb 2012||27 Sep 2012||Asahi Intecc Co., Ltd.||Guidewire|
|US20140121648 *||11 Jun 2012||1 May 2014||Koninklijke Philips N.V.||Composite fiber guidewires|
|Clasificación de EE.UU.||600/585, 29/428|
|Clasificación internacional||A61M25/01, A61B6/00, A61B5/055, A61M25/00, A61M25/09, A61B5/05|
|Clasificación cooperativa||A61M25/09, Y10T29/49826, A61M2025/09083, A61M2025/09166|
|28 Ago 2012||FPAY||Fee payment|
Year of fee payment: 4
|4 Nov 2016||REMI||Maintenance fee reminder mailed|
|24 Mar 2017||LAPS||Lapse for failure to pay maintenance fees|
|16 May 2017||FP||Expired due to failure to pay maintenance fee|
Effective date: 20170324